CN102655809B - Apparatus for phase-contrast imaging comprising a displaceable X-ray detector element and method - Google Patents
Apparatus for phase-contrast imaging comprising a displaceable X-ray detector element and method Download PDFInfo
- Publication number
- CN102655809B CN102655809B CN201080055839.5A CN201080055839A CN102655809B CN 102655809 B CN102655809 B CN 102655809B CN 201080055839 A CN201080055839 A CN 201080055839A CN 102655809 B CN102655809 B CN 102655809B
- Authority
- CN
- China
- Prior art keywords
- ray
- ray detector
- optical grating
- displacement
- phase
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
- 238000003384 imaging method Methods 0.000 title claims abstract description 48
- 238000000034 method Methods 0.000 title claims description 19
- 238000006073 displacement reaction Methods 0.000 claims abstract description 60
- 230000003287 optical effect Effects 0.000 claims description 54
- 230000000007 visual effect Effects 0.000 claims description 32
- 238000003325 tomography Methods 0.000 claims description 17
- 230000015572 biosynthetic process Effects 0.000 claims description 12
- 238000003786 synthesis reaction Methods 0.000 claims description 12
- 239000013598 vector Substances 0.000 claims description 10
- 238000005516 engineering process Methods 0.000 abstract description 4
- 230000033001 locomotion Effects 0.000 description 9
- 230000010363 phase shift Effects 0.000 description 9
- 238000010521 absorption reaction Methods 0.000 description 6
- 230000008569 process Effects 0.000 description 6
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 5
- 230000008859 change Effects 0.000 description 5
- 230000000694 effects Effects 0.000 description 5
- 229910052710 silicon Inorganic materials 0.000 description 5
- 239000010703 silicon Substances 0.000 description 5
- 230000001427 coherent effect Effects 0.000 description 4
- 238000009607 mammography Methods 0.000 description 4
- 230000005540 biological transmission Effects 0.000 description 3
- 238000005530 etching Methods 0.000 description 3
- 238000003306 harvesting Methods 0.000 description 3
- LFEUVBZXUFMACD-UHFFFAOYSA-H lead(2+);trioxido(oxo)-$l^{5}-arsane Chemical compound [Pb+2].[Pb+2].[Pb+2].[O-][As]([O-])([O-])=O.[O-][As]([O-])([O-])=O LFEUVBZXUFMACD-UHFFFAOYSA-H 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- 230000005855 radiation Effects 0.000 description 3
- 230000009467 reduction Effects 0.000 description 3
- 239000006096 absorbing agent Substances 0.000 description 2
- 230000002238 attenuated effect Effects 0.000 description 2
- 238000001514 detection method Methods 0.000 description 2
- 239000010931 gold Substances 0.000 description 2
- 230000001965 increasing effect Effects 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000002161 passivation Methods 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 240000008042 Zea mays Species 0.000 description 1
- 235000005824 Zea mays ssp. parviglumis Nutrition 0.000 description 1
- 235000002017 Zea mays subsp mays Nutrition 0.000 description 1
- 230000002745 absorbent Effects 0.000 description 1
- 239000002250 absorbent Substances 0.000 description 1
- 210000003484 anatomy Anatomy 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 238000002591 computed tomography Methods 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 235000005822 corn Nutrition 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 230000005670 electromagnetic radiation Effects 0.000 description 1
- 238000009713 electroplating Methods 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 239000000284 extract Substances 0.000 description 1
- 239000004744 fabric Substances 0.000 description 1
- 238000005562 fading Methods 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 238000005286 illumination Methods 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 239000000523 sample Substances 0.000 description 1
- 238000005070 sampling Methods 0.000 description 1
- 229910052711 selenium Inorganic materials 0.000 description 1
- 239000011669 selenium Substances 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 230000003068 static effect Effects 0.000 description 1
- 230000000699 topical effect Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/032—Transmission computed tomography [CT]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4021—Arrangements for generating radiation specially adapted for radiation diagnosis involving movement of the focal spot
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/48—Diagnostic techniques
- A61B6/484—Diagnostic techniques involving phase contrast X-ray imaging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4064—Arrangements for generating radiation specially adapted for radiation diagnosis specially adapted for producing a particular type of beam
- A61B6/4092—Arrangements for generating radiation specially adapted for radiation diagnosis specially adapted for producing a particular type of beam for producing synchrotron radiation
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Radiology & Medical Imaging (AREA)
- Molecular Biology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- High Energy & Nuclear Physics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Pulmonology (AREA)
- Theoretical Computer Science (AREA)
- Apparatus For Radiation Diagnosis (AREA)
- Analysing Materials By The Use Of Radiation (AREA)
Abstract
The present invention relates to X-ray image acquisition technology in general. Employing phase-contrast imaging for X-ray image acquisition may significantly enhance the quality and information content of images acquired. However, phase- contrast information may only be obtainable in a small detector region, possibly being too small for a sufficient field of view for specialized X-ray imaging applications. Accordingly, an apparatus for phase-contrast imaging is provided that may allow the acquisition of an enlarged field of view. According to the present invention an apparatus (1) for phase-contrast imaging is provided, comprising an X-ray source (2), an X-ray detector (12) element having a detector size, a beam splitter grating (8) and an analyzer grating (10). An object (6) is arrangeable between the X-ray source (2) and the X-ray detector (12). The beam splitter grating (8) and the analyzer grating (10) are arrangeable between the X-ray source (2) and the X-ray detector (12). X-ray source (2), the beam splitter grating (8), the analyzer grating (10) and the X-ray detector (12) are operatively coupled such that a phase-contrast image of the object (6) is obtainable. The apparatus (1) is adapted for acquiring a phase-contrast image having a field of view larger than the detector size. The X-ray detector element (12) is displaceable and by the displacement of the X-ray detector (12) a phase-contrast image of the field of view is obtainable.
Description
Technical field
Present invention relates in general to X-ray image acquisition.More specifically, the present invention relates to employing to match the image acquisition of (phase-contrast).Specifically, the present invention relates to and a kind ofly comprise the equipment for the imaging that matches of movable X-ray detector element, a kind of x-ray system, a kind of method for gathering disparate images information and in x-ray system, one of CT system and tomography synthesis system, use the equipment for the imaging that matches.
Background technology
In X-ray image acquisition technology, examine object, such as patient, be positioned at X-ray generator or between x-ray source (such as X-ray tube) and X-ray detector.X-ray source produces fan-beam or cone-beam on X-ray detector direction, and this may be adopt collimating element to realize.Be arranged in the examine object in X-radiation path according to its internal structure spatially attenuated X-ray beams.The X-radiation be spatially attenuated arrives soon after X-ray detector, wherein determines the intensity distributions of X-radiation and converts the signal of telecommunication to subsequently, for process and display radioscopic image further.
X-ray generator and X-ray detector can be arranged in frame, to rotate around examine object.By providing consistent rotation, gathering different radioscopic images relative to examine object change aligning and orientation subsequently, the three-dimensional reconstruction of object external morphology can be obtained.
But, even if certain object also only may have a small amount of decay or the difference in attenuation of X-radiation within the different tissues of object inside, thus acquisition has the decling phase of low contrast when uniform radioscopic image, thus the independent element of examine object inside can not be distinguished.Although the zones of different within object may have similar attenuation properties, they may in the phase place having influence on the X-radiation penetrating object to a greater extent.
So, the imaging that matches can be adopted to carry out visual to the phase information by the X-radiation of examine object, especially coherent X-ray.Except the X-ray transmission imaging only considering the amplitude fading of X-radiation, the imaging that matches not only can determine the absorbent properties of examine object along projection line, and can determine the phase shift of transmission X-ray.So the phase shift detected can provide extraneous information, and extraneous information can be used for enhancing contrast ratio, determines material composition, the reduction of X-radiation dosage may be realized.
Due to the phase place of ripple directly can not be measured, therefore can adopt and change phase shifting into intensity modulated by the interference of two or more ripples.
In differential contrast imaging, use cone-beam geometry may form restriction to the useful size of X-ray detector element, be especially parallel to optical axis with its groove and when aiming at phase place and/or absorption grating.In the distance apart from the about 1m of x-ray source, the point that phse sensitivity significantly declines relative to imaging system central area approximately departs from optical axis ± 3cm.
For some application, such as, imaging of medical application, check imaging applications or safe imaging applications, at least on a direction of two-dimensional x-ray images lower than the visual field of 6cm, may be too little, and unreasonable in feasibility.
So, may wish to increase visual field when employing matches imaging.
Summary of the invention
Therefore, to provide according to independent claims a kind of have increase visual field the equipment for the imaging that matches, a kind of comprise equipment for the imaging that matches x-ray system, a kind of method for gathering disparate images information and in x-ray system, one of CT system and tomography synthesis system, use equipment for the imaging that matches.
According to one exemplary embodiment of the present invention, provide a kind of equipment for the imaging that matches, it comprises x-ray source, has the X-ray detector element of detector size, the first optical grating element and the second optical grating element.Object can be arranged between x-ray source and X-ray detector, and the first optical grating element and the second optical grating element also can be arranged between x-ray source and X-ray detector.Operability is coupled the first optical grating element, the second optical grating element and X-ray detector, thus makes it possible to the disparate images obtaining object.Disparate images comprises the disparate images information that visual field is greater than described detector size.X-ray detector element can displacement, wherein, by making X-ray detection displacement, can obtain the disparate images of visual field.
According to another one exemplary embodiment of the present invention, provide a kind of x-ray system, it comprises according to the equipment for the imaging that matches of the present invention.
According to another one exemplary embodiment of the present invention, provide a kind of method gathering disparate images information, it comprises the steps: that under first phase step state, gather first matches image information, make at least one displacement in examine object and x-ray source of X-ray detector elements relative, tilt and/or rotate, and the first optical grating element and the second optical grating element are relative to each other shifted.Gather second to match image information, it comprises second phase step state.
According to another one exemplary embodiment of the present invention, use according to the equipment for the imaging that matches of the present invention at least one in x-ray system, CT system and tomography synthesis system.
In order to obtain the phase information of X-ray beam, interferometer can be adopted.Preferably, relevant X-radiation is by examine object, and arrive soon after X-ray detector.Due to directly phase information can not be measured, therefore can adopt two or more wavefront long or mutual hint that disappears mutually mutually, may make it possible to detect intensity modulated by X-ray detector.
Corresponding interference can be obtained by providing phase-shifted grating or beam splitter grating between examine object and X-ray detector.X-radiation by beam splitter grating, thus obtains interference pattern after beam splitter grating, comprises the information of the phase shift of the relative position of its minimum and maximum within X-ray beam, i.e. the corresponding topical intensity of X-ray beam.The intensity pattern of gained comprises minimum and the maximum of the distance usually with large approximate number micron.
But, X-ray detector can only comprise approximately ~ resolution of 50 to 150 μm, so the corresponding fine structure of produced interference pattern may not be differentiated.Therefore, can adopt phase analyzer grating or absorber grating, comprise the non-periodic pattern of transmission and absorption strip member or trench region and occlusion area, it is periodically similar to interference pattern.
By only illumination beam splitter device grating, even if when there is no analyser gratings, also interference pattern can be produced in the position of analyser gratings.Thus, owing to have employed X-ray detector element, may only Water demand device grating, this does not provide sufficiently high spatial resolution with the striped of direct detection interference pattern or beam splitter grating.Therefore, analyzer can be adopted.At a phase place stepping position, allow striped maximum by detector, after lateral displacement, this maximum may be absorbed in golden groove.
By the similar periodicity of analyser gratings, on the surface of X-ray detector, More's pattern can be produced at analyser gratings rear.Corresponding More's pattern may have significantly larger periodicity, so the X-ray detector that the rate that can be resolved is approximately 50 to 150 μm detects.In order to obtain disparate images, especially in order to obtain differential phase shift, possible Water demand device grating lateral shift, namely perpendicular to the sub-fraction (being approximately 1 μm) analyser gratings and the grid of beam splitter grating or the direction of band offseting grating space p, these gratings are arranged to be arranged essentially parallel to grating strip.Such as, can by from a grating gap or trench region to the position change in grating gap subsequently approximately such as 4 times or 8 times.The skew of the respective transversal of a fraction of grating space p can be called phase place stepping.So, in single phase place stepping situation, comprise independent phase place step state by the X-ray beam of grating.
Can from each position for analyser gratings, the intensity modulated observed in X-ray detector element at two grid rears during such as, phase place stepping for each phase place step state actual measurement extracts phase shift.Incide the angle of incidence on grating due to X-ray, can see, relative to the groove extending transverse to grating, off-axis position is larger, and visibility is less.In order to ensure fully high visibility, thus in order to ensure that X-ray detector has abundant high detectivity to X-ray phase place, visual field can be restricted to the size of about 6cm, such as system length, distance between x-ray source and X-ray detector element is about 1m, and energy is about 20-30kVp.Can find out, the scheme increasing visual field is mobile X-ray detector, thus obtains multiple subregions of visual field subsequently.Due to each position for X-ray detector, phase place stepping may be needed, that is, it such as 4 or 8 times there is the independent image acquisition of out of phase step state, so may be the process grown very much that the corresponding movement of X-ray detector, displacement, inclination or rotation and respective phase stepping are combined.
Visual field is at least less than 6cm on a direction or expansion (extension), use planar detector may require can match in imaging, such as differential matches in mammography and is restricted.The scheme overcoming visual field restriction can be adopt multi-disc block (multi-tile) detector, such as comprise the detector of multiple detector element (may incline towards each other relative to detector plane), and/or at visual field scanning overhead sheet block or detector, thus gather multiple successive image, form larger visual field.
In the absorption contrast projection imaging of routine, superpose the numerous object structure along incident X-rays direction in the picture.This usually may make to determine independent complex structure, thus reduces the readability of corresponding radioscopic image.By total radiation dose that distributes on the view of several angles to improve the depth information about object internal structure, the improvement of picture quality can be realized.Corresponding technology can be called that tomography synthesizes.Corresponding system may need to arrange x-ray source and X-ray detector in frame, to rotate around examine object.
Even if matching in imaging, single projection also can comprise the structure of superposition, thus also can benefit from tomography synthetic work pattern.Therefore, the system that matches can carrying out tomography synthesis is adopted can to overcome the readable problem reduced by superposition anatomical structure.
Match in imaging in the imaging that matches, especially differential, need fully large fringe visibility, such as fully large intensity modulated, this may bring restriction to the relative motion degree of freedom between x-ray source and grating.Usually, x-ray source only can be allowed to carry out relative movement along linear grating groove.So, mobile by providing tomography to synthesize on the direction of silicon grid groove being parallel to grating, the compatibility that can realize tomography synthesis and match between imaging.So, can find out it is advantageous that the X-radiation measured within the plane perpendicular to linear grating groove can not be elevated to more than certain level to the angle of incidence on grating during tomography scan synthesis.
By mobile X-ray detector thus by visual field scanning X-ray detector come extended field of view may to need for visual field within each position of X-ray detector carry out phase place stepping.Such as, at ad-hoc location, may need the phase place stepping of 4 or 8 image acquisition step, each step has different phase place step states.Subsequently, X-ray detector displacement can be made previously to arrange substantially adjacent subarea in acquisition field of view with within visual field, adopt the phase place stepping with 4 or 8 image acquisition step subsequently, with the disparate images information in acquisition field of view second subarea.
But, may not need to make X-ray detector displacement in X-ray detector self expansion or width size, but its only displacement X-ray detector or its sub-fraction expanded for the effective area that X-ray gathers can be made, such as 1/4 or 1/8, the radioscopic image information of simultaneous phase place the stepping not only slightly different subarea of acquisition field of view (may overlapping with previous subarea 3/4 or 7/8), but also there is the out of phase step state adopting and match and produce subsequently needed for radioscopic image information.
By in any one in X-ray detector, beam splitter grating or analyser gratings, even the extra translation member on another source grating can may realize corresponding displacement.Make X-ray detector, beam splitter grating and analyser gratings be subjected to displacement simply, and do not change each element relation to each other, may cause gathering image information and carry out matching imaging.
From the viewpoint of reality, such as, for manufacture according to for equipment of the present invention, the groove of grating can be preferably perpendicular to the flat surfaces of X-ray detector.
Conventionally, beam splitter grating and analyser gratings can be manufactured with silicon wafer (silicon waver).For analyser gratings, extra electroplating process may be needed, to use high-selenium corn material, such as golden filling groove.This manufacture process can, from applying passivation layer, then be such as etchant flow.The region that passivation layer covers can not affect by etching process, thus obtains usually required groove pattern.But, etched trench on the direction different from the direction perpendicular to waver surface may be difficult to.To match system for cone-beam X-ray, etching direction may depend on the position on silicon wafer strongly, thus makes it possible to groove to focus on the predefine position being designed to overlap with x-ray source position after a while.
Can find out, when departing from optical axis and being about 6cm scope, corresponding layout is especially had a responsibility for reduction structure visibility.Specifically, between x-ray source and X-ray detector, detector size may be restricted to about 6cm, such as, when about 20-30keV by the distance of about 1m.
In order to overcome the corresponding restriction of detector size, spreaded type (tiled) detector can be adopted, each detector element inclined towards each other relative to the focal spot of x-ray source or X-ray generator may be comprised.The corresponding layout of detector element can be regarded as and be orientated to the surface normal of each detector element respectively towards x-ray source and focal spot thereof, thus in the direction, be like this when at least considering in perpendicular to the two-dimensional section of linear grating groove.
Therefore, each detector element can be regarded as and have its oneself independent optical axis, this optical axis points to x-ray source and also aims at it.Detector size can be restricted to about 6cm to regard as and be applicable to each independent detector element.But, adopt in the search coverage of the X-ray detector be made up of at least two or more detector element between sheet block or detector element and introduce gap.Within gap, image acquisition cannot be performed.At the specific area of X-ray image acquisition, such as, in mammography applications, the structure of tens to 100 μm be detected, cause image information loss may be unacceptable owing to cannot detect within gap between X-ray detector element.
Because the imaging that matches has required the relative position utilizing grating, so utilize independent phase place step state, repeatedly, the every bar geometry ray measured from x-ray source to detector pixel for such as 4,8 or 9 times, therefore phase place stepping can combine with mobile, movement is such as the combination of the displacement of X-ray detector, inclination or rotation and phase place stepping.
By adopting corresponding movement, so each geometric array only overlaps once with the gap of tiled detector array, thus provide measurement fully repeatedly for every bar geometry ray, for the follow-up generation of phase retrieval and disparate images.Such as, between the detector difference needed for phase retrieval is irradiated, detector entirety can move using focal spot as rotating shaft, especially tilts towards focal spot or x-ray source, thus the surface normal of each detector element can be concentrated to the focal spot of x-ray source.
By adjusting rotation or the movement of detector, following effect can be realized: every bar geometry ray only overlaps once with the gap between sheet block between whole Harvest time, so all phase retrieval may be carried out for whole detector region, the gap between detector element can not be seen after image acquisition.Such as, when being needed the phase place stepping of N=8 independent phase place step state by corresponding rotation or the every bar geometry ray of mobile employing, if measured as follows by detector moving for each step, all geometry rays are by measured 8 times
Wherein, D is detector width, and G is gap width.So altogether need 9 image acquisition.In addition, need to guarantee that displacement x is greater than gap, this requirement easily meets, because compared with clearance G, usual D is larger: D>>G.
Such as, can realize slight overlapping by implementing following formula:
Δx≥2G
The medical image of acquisition of diagnostic quality needs the specific visual field seamlessly covered around given objects usually.Can by adopting large area pixel probe unit, so adopt X-ray detector automatically to realize this covering, thus make for be positioned at detector or at least detector pixel cover solid angle within all adjacent geometry ray, image-forming information all can be used.This may be the situation of several detector element arranged adjacent one another, especially may comprise the situation of gap or spacing distance.After this, geometry ray can be considered as the static line be attached in the reference frame of objects.So geometry ray can be the fixing sight line overlapped with X-ray detector component pixel, pixel column or pixel column in a kind of situation or image acquisition step.In order to obtain suitable image information, such as, for phase contrast imaging, may need to gather identical geometry ray, especially relative to the specific internal of x-ray source and examine object.Further contemplate the distance between x-ray source and corresponding focal spot thereof, corresponding geometry ray especially can have the dimension extension relevant to the size of X-ray detector component pixel.
When adopting coherent X-ray source, the imaging that matches can be implemented valuably.But, due to especially coherent X-ray source may be provided by means of only such as synchrotron, therefore in the course of the beam of X-ray, another grating can be adopted between x-ray source and object, source grating, for generation of multiple independent coherent X-ray source.
In addition, two absorption gratings can also be adopted to replace a phase grating and an absorption grating carries out matching imaging.So the phase place stepping according to present patent application also may be needed.
And, may need dynamically to collimate X-radiation relative to mobile X-ray detector element, to guarantee that the X-radiation only allowing to detect passes through object.
In addition, can each along the direction of propagation focused light grid block of X-ray cone-beam.Hereinafter, especially with reference to device description other embodiments of the present invention for the imaging that matches.But, these illustrate and are also applicable to x-ray system, for gathering in the method for disparate images information and at least one in x-ray system, CT system and tomography synthesis system the equipment used for the imaging that matches.
Also by object placement between the first optical grating element and the second optical grating element, specifically can be unlikely between beam splitter grating and analyser gratings.
It should be pointed out that any change and the exchange of single or multiple feature between claim and especially advocated entity can be expected, and present patent application scope and open within.
According to another one exemplary embodiment of the present invention, at least one that can comprise in the focal spot of described x-ray source and described x-ray source of the displacement of described X-ray detector element rotates.
In rotary moving by X-ray detector element, the focal spot of x-ray source and/or x-ray source keeps substantially identical relative to the angle of the groove structure of optical grating element, especially groove structure sidewall during collection disparate images information.Preferably, this angle is zero relative to the sidewall of optical grating element substantially, and at least relative to the center of optical grating element, the sidewall that the cone-beam of X-radiation or fan-beam are directly parallel to optical grating element is incident.
According to another one exemplary embodiment of the present invention, beam splitter grating and analyser gratings can displacements toward each other, and to provide phase place stepping, and/or beam splitter grating and analyser gratings can be arranged to parallel to each other and be parallel to X-ray detector element.
Adopt the independent disparate images information of phase place stepping collection, such as, intensity modulated during phase place stepping, the expression of the internal structure of rebuilding examine object can be allowed.The displacement of beam splitter grating and analyser gratings preferably makes to arrange multiple displacement within grating one-period.Especially 1/4 of such as screen periods or the displacement of 1/8 is it is beneficial that adopted.
According to another one exemplary embodiment of the present invention, x-ray source can relative to beam splitter grating, analyser gratings and/or the displacement of X-ray detector element.In addition, x-ray source, beam splitter grating, analyser gratings and X-ray detector element can rotate around examine object.
Such displacement can be regarded as location x-ray source and focal spot, to produce X-radiation respectively in relative to the difference arrangement of examine object and external morphology thereof.So, by arranging x-ray source by different way relative to object, the collection of tomography composograph can be realized.
According to another one exemplary embodiment of the present invention, at least one in described first optical grating element and described second optical grating element can comprise groove structure, wherein, described groove structure can comprise the first expansion being parallel to described groove structure and groove respectively, and wherein, the displacement of described x-ray source can be parallel to described first expansion.
So, at least for single width disparate images, during gathering disparate images information, the angle between x-ray source and optical grating element sidewall can be kept substantially constant.
According to another one exemplary embodiment of the present invention, described X-ray detector element can be displaced to the second position in the second subarea for acquisition field of view from the primary importance in the first subarea for acquisition field of view, described beam splitter grating and described analyser gratings can displacements toward each other, to provide first phase step state in first position and to provide second phase step state in second position.
In other words, when reorientating detector element and beam splitter grating and analyser gratings, further beam splitter grating and analyser gratings are reorientated relative to one another, the sub-fraction of the screen periods of one of beam splitter grating and analyser gratings may be differed, to obtain the difference of phase place stepping, thus obtain different phase place step states when gathering the first image information in first position and gather the second image information in second position to allow to rebuild disparate images information.
According to another one exemplary embodiment of the present invention, this equipment also comprises at least two X-ray detector elements, at least two beam splitter gratings and at least two analyser gratings.At least two X-ray detector elements adjacent layout also can make its separately spacing distance, and it may form the gap between the detector element pixel of at least two detector elements, thus forms the region that possibly cannot gather image information.Each surface normal vector that can be included on described x-ray source direction of described at least two X-ray detector elements, and in spacing distance, cannot image information be gathered.
By adopting at least two or more X-ray detector element, also may adopt multiple beam splitter grating and the analyser gratings each other with respective angles, the visual field of the X-ray detector comprising at least two detector elements can be increased, such as, increase to more than 6cm.At least two beam splitter gratings and at least two analyser gratings can be individual components, or also can adjacent layout thus be connected to each other.It will also be appreciated that, one of multiple beam splitter grating and analyser gratings form modular elements, the autoorientation being parallel at least two X-ray detector elements may be had, wherein other multiple beam splitter gratings and analyser gratings are the individual component being separated from each other and separating with other gratings corresponding, to allow to carry out phase place stepping.
Specifically, at least in 2 dimensional planes being parallel to linear grating groove, the surface normal vectors directed focal spot of each center of X-ray detector element can be thought.
More preferably, can provide and have cylindrical or spherical detector element, beam splitter grating and/or analyser gratings, wherein x-ray source is arranged in focus, thus equal with the surface distance of X-ray detector element, beam splitter grating and/or analyser gratings.
According to another one exemplary embodiment of the present invention, the size of at least two detector elements can comprise the visual field of image to be collected substantially.
So, by providing X-ray detector (each detector element such as has 6cm or less width) with the detector element of at least two adjacent layouts, the image of the visual field larger than single detector element can be gathered.So, can acquisition field of view ratio larger image admissible relative to the size of independent detector element usually.
According to another one exemplary embodiment of the present invention, x-ray source relative to examine object displacement, and can maintain the orientation of surface normal vector on x-ray source direction of at least two X-ray detector elements during the displacement of x-ray source.
Maintain the tomography synthesis disparate images that the aligning of X-ray detector element on x-ray source direction can allow acquisition field of view larger than single detector element when making x-ray source displacement, such as, visual field is greater than 6cm, and such as 12,18,20,24 or 30cm.At least perpendicular in the two dimensional surface of linear grating groove, thus the orientation of surface normal vector on x-ray source direction can be maintained in the plane being parallel to surface normal vector.
According to another one exemplary embodiment of the present invention, described at least two X-ray detector elements can be displaced to the second position for gathering the second disparate images and/or orientation from the primary importance and/or orientation for gathering the first disparate images, and wherein, another each displacement toward each other corresponding of each of at least two the first optical grating elements and at least two the second optical grating elements can be made, to provide first phase step state when gathering described first disparate images, and provide second phase step state when gathering described second disparate images.
Equally, by providing a fraction of displacement in the cycle of one of two gratings, different phase place step states can be provided when collection first disparate images and the second disparate images.
Second each with the corresponding optical grating element of the first grating is associated to gather disparate images information.
According to another one exemplary embodiment of the present invention, at least two X-ray detector elements displacement described in can making between collection two different disparate images, inclination and/or rotation, thus the image information loss that cannot gather in spacing distance is minimized, especially wherein, the displacement of at least two X-ray detector elements, inclination and/or rotation can be made during collection disparate images, thus make every bar geometry ray fall at most inevitable gap between detector element.
Therefore, two detector elements can be moved, thus make in such as 4 or 8 independent image acquisition step, in the disparate images of the successive times adopting independent phase place step state gathers, every bar geometry ray only overlaps once with the gap between at least two detector elements and spacing distance respectively.In other words, if need the measurement for every bar geometry ray for 8 times with out of phase step state, then execution 9 different measurings may be needed.So, when adopting out of phase step state to carry out n different measuring for corresponding geometry ray, for every bar geometry ray, n-1 different measuring value at least can be obtained, for determining disparate images subsequently.
According to another one exemplary embodiment of the present invention, this equipment can also comprise source grating.
By in the path of X-ray beam between x-ray source and object providing source grating, can adopt may incoherent x-ray source or at least part of incoherent x-ray source, for the imaging that matches.
According to another one exemplary embodiment of the present invention, step b and c can be repeated predefined number of times, especially repeat 8 times, thus form collection period, wherein, in collection period, every bar geometry ray at most only can overlap once with the gap between sheet block.
By adopting corresponding collection period, the basic uniform signal to noise ratio of gathered whole image can be realized.
These and other aspects of the present invention will become apparent from embodiment described below and be set forth with reference to it.
Hereinafter with reference to the following drawings, one exemplary embodiment of the present invention is described.
Illustration in accompanying drawing is only schematic.In different figures, for similar or identical element provides similar or identical Reference numeral.
Accompanying drawing not drawn on scale, but ratio qualitatively can be described.
Accompanying drawing explanation
Fig. 1 a-c shows the one exemplary embodiment according to the equipment for the imaging that matches of the present invention;
Fig. 2 shows the one exemplary embodiment according to interference pattern of the present invention;
Fig. 3 a, b show the exemplary disparate images gathered according to the present invention;
Fig. 4 shows the exemplary visibility according to the interference fringe relative to detector element pixel off-axis position of the present invention;
Fig. 5 a, b show the one exemplary embodiment that tomography according to the present invention synthesizes;
Fig. 6 a, b show according to the three peacekeeping two-dimensional representation comprising the one exemplary embodiment of the X-ray detector of multiple detector element of the present invention;
Fig. 7 a-d shows the exemplary displacement of focal spot according to the present invention relative to spreaded type X-ray detector;
Fig. 8 shows the one exemplary embodiment according to the method for gathering disparate images information of the present invention.
Reference numerals list
1 for the equipment of phase contrast imaging
2X radiographic source
4 source grating G
0
5X radiation
6 objects
7 optical axises
8 beam splitter grating/phase grating G
1
10 analyser gratings/absorber grating G
2
12 (a-e) X-ray detector (element)
14 focal spots
16 Linear-movings
18 rotate
20 gaps
22a, b, c surface normal vector
30 for gathering the method for disparate images information
32STEP: gather first and to match image information
34a STEP: displacement, inclination and/or rotational x-ray detector element
34b STEP: make the displacement toward each other of beam splitter grating and analyser gratings
36STEP: gather second and to match image information
Detailed description of the invention
With reference now to Fig. 1 a-c, show the one exemplary embodiment according to the equipment for the imaging that matches of the present invention.
Fig. 1 a shows the three dimensional representation of the one exemplary embodiment of the equipment for the imaging that matches.Be adjacent to arrange sizable x-ray source 2 with source grating 4.Owing to can think that x-ray source 2 is incoherent due to its size relative to the wavelength of institute's emitted radiation, therefore adopt source grating G
04 provide multiple single relevant x-ray source, as shown in two arrows in Fig. 1 b.
Launch X-radiation 5 from x-ray source 2 along the direction of optical axis 7, it may form fan-beam or the cone-beam of X-ray.The respective shapes of not shown X-ray beam in Fig. 1 a.
X-radiation 5 arrives object 6, penetrates object 6, and arrive soon after beam splitter grating G
18.The groove of beam splitter grating 8 or gap are relative to the entity area of beam splitter grating, i.e. occlusion area, changes the electromagnetic radiation phase place passed through.Therefore, phase shift is realized
especially π.
Analyser gratings 10G
2be arranged in beam splitter grating G
1between 8 and X-ray detector 12.Distance between source grating and beam splitter grating 8 is illustrated as l, and the distance between beam splitter grating 8 and analyser gratings 10 is illustrated as distance d.From beam splitter grating 8G
1the multiple ripples launched along the direction of X-ray detector arrive analyser gratings 10G
2, on the surface of X-ray detector 12, produce intensity modulated pattern (see Fig. 2) subsequently.
By offseting beam splitter grating 8 relative to analyser gratings 10, thus make grating displacement toward each other, especially displacement screen periods p
1or p
2sub-fraction, can obtain by image detector 12 multiple intensity modulated that phase place stepping causes because phase place step state is different between independent phase place stepping separately, i.e. G
1relative to G
2aligning.Therefore, by multiple More's pattern, the radioscopic image of examine object can be produced.According to the Talbot order selected in interferometer design, distance l can be approximately 50-150cm, and distance d can be approximately 2-20cm.
With reference now to Fig. 1 c, show grating G
0to G
2exemplary cross section.Gold (Au) is specifically used to fill grating G
0and G
2.Grating G can be realized to provide the groove of grating by etching silicon sill
1and G
2.The screen periods p of source grating
0200 μm even less can be approximately, G
1screen periods p
1exemplarily can be 4 μm, and G
2screen periods p
2can it be exemplarily 2 μm.
With reference now to Fig. 2, show the one exemplary embodiment according to interference pattern of the present invention.
Fig. 2 depicts beam splitter grating G
18 and analyser gratings G
2the interference pattern generated between 10, illustrates characteristic distance d
1, d
2and d
3the self-imaging (Talbot effect) of grid.The relative position of minimum and maximum especially may depend on and incides beam splitter grating G
1on wavefront phase shift.D
1especially can be approximately several centimetres.If single color plane ripple incides on beam splitter grating, this brings out
especially π phase shift, then intensity is divided into two major diffraction levels, eliminates zeroth order.Interference effect causes inciding G
1on wavefront at G
1the self-imaging at discrete distance place, downstream.This effect is called as Talbot effect.Such as, at distance p1^2/8 λ (lambda) place, by G
1the phase-modulation of the incident wavefront caused converts the intensity modulated with double frequency to.Analyser gratings is sampled to these modulation and allows the phase gradient that measuring object is caused X-ray wavefront by phase place stepping.
With reference now to Fig. 3 a, b, depict the exemplary disparate images gathered according to the present invention.
In fig. 3 a, by phase place stepping, adopt four phase place steps, thus adopt four independent phase place step state a-d, gather the exemplary four width images comprising the object of independent bubble.Distance x
1-x
4relate to the grating G in order to produce intensity modulated
1relative to G
2displacement.From x
1-x
4complete movement at grating G
2one-period within (<2 μm).Along the direction x deviation absorption device grid or the analyzer grid G that are parallel to grating planar
210.Can from such as the sampling location x of four Fig. 3 a
1-x
4the phase shift recording intensity modulated
the Wave-front phase extracting two position sets and " 2 " place is poor.
With reference now to Fig. 4, depict the exemplary visuality according to the interference fringe relative to detector element pixel off-axis position of the present invention.
The deterioration of fringe visibility along with detector pixel off-axis position can be obtained from Fig. 4.Can think that the fringe visibility of .5 or larger is that Computer image genration and process provide and reasonably match.According to the grating G providing more deep trench (such as 35 μm) in grating
2the optical grating construction height H of (see Fig. 1 c)
2, provide three kinds of functions in the diagram, the more shallow grating depth H relative to such as 15 μm
2achieve the off-axis visibility of reduction.As can be seen from Figure 4, both sides collimation must lower than 6cm, so Δ x should <3cm, thus by matching in imaging, the useful size of planar detector that such as differential matches in mammography is restricted to about 6cm.
With reference now to Fig. 5 a, b, depict the one exemplary embodiment that tomography according to the present invention synthesizes.
Fig. 5 a, b depict match tomography synthesis two kinds may realize.In fig 5 a, the cone-beam of X-radiation 5 is adopted linearly mobile 16 to make x-ray source 2 or focal spot 14 displacement, for the different x-ray view gathered by object 6 relative to object 6.
Mobile 16 are basically parallel to the linear grating groove for the imaging that matches, shown in its non-Fig. 5 a, b.
Because X-ray detector 12 has the expansion of the such as 6cm perpendicular to linear grating groove, X-ray detector is therefore needed to carry out scanning by visual field FOV mobile with the radioscopic image obtaining fully large object 6.Such as, in mammography applications, the visual field being typically 20 × 30 or 30 × 40cm may be needed.
In fig 5 a, can think that x-ray source 2 or focal spot 14 move independent of X-ray detector 12, X-ray detector 12 only performs the visual field scanning shown in arrow in Fig. 5 a and moves.
Another kind of enforcement can be found out in figure 5b.X-ray source 2/ focal spot 14 and X-ray detector 12 such as can be arranged on to rotate around axle 18 in frame, therefore around both object 6 rotational x-ray source 2 and X-ray detector 12.Movement accordingly can be moved with the rule in computed tomography system and compare.
In figure 5b, so X-ray tube and X-ray detector rotate around object 6 simultaneously.Equally, implement that X-ray detector 12 moves relative to visual field scanning on each independent position of X-ray detector, the another kind of visual field scanning of phase place stepping moves, for collection contrast information.Therefore, X-ray detector 12 can displacement its extend sizes basic, such as 6cm, thus adopt 4,8 or 9 exemplary phase place steps to provide phase place stepping image information collecting, or can the sub-fraction of the only above-mentioned 6cm of displacement, 1/4,1/8 or 1/9 of such as its 6cm expansion, accompanying event stepping simultaneously, to provide independent phase place step state.
In order to implementing phase stepping in a continuous manner, such as, grating G
1can allegretto carry out visual field scanning than other elements of travelling arm to move, such as, by detector/G
1/ G
2the extra translation member that cloth is set up.Such as, in other words, for each displacement of X-ray detector 12, according to linear or in rotary moving, by grating G
1the same distance of displacement or angle, add extra Δ value, with the phase place step state providing another new.
With reference now to Fig. 6 a, b, depict according to the three peacekeeping two-dimensional representation comprising the one exemplary embodiment of the X-ray detector of multiple detector element of the present invention.
In Fig. 6 a, depict the spreaded type X-ray detector comprising exemplary five detector element 12a-e.X-ray source 2 launches the cone-beam of X-ray 5, when Fig. 6 a, can think the visual field that its basic comprising is expected.
Between independent detector element 12a-e, arrange gap 20, its size may be approximately 1mm to 100 μm.By typical resolution, thus X-ray detector component pixel size can be considered as 50 to 250 μm.
In Fig. 6 a, unshowned collimating element can dynamically collimate fan-beam 5, to correspond essentially to region or the current location of X-ray detector 12.
With reference now to Fig. 6 b, depict the two dimensional image cross section of A-A' along the line, which show only detector element 12b-d.Gap 20 is arranged between detector 12b and c, and between detector element 12c and d.Surface normal vector 22a, b, c, along the direction of focal spot 2, may stride across focal spot 2, are arranged on each surface of independent X-ray detector element 12b, c, d.Independent detector element 12b, c, d incline towards each other angle [alpha] and β, and these angles especially can be equal.Not shown grating G in Fig. 6 a, b
1, G
2and possible G
0.Can find out in Fig. 6 a, b, arrange the gap 20 between detector element 12a-e, thus make can not gather image information within gap.
With reference now to Fig. 7 a-d, depict the exemplary displacement of focal spot according to the present invention relative to spreaded type X-ray detector.
In Fig. 7 a-7d, move focal spot 14/X radiographic source 2 linearly, gather to carry out tomography synthesis according to Fig. 5 a.It is also feasible for further rotating according to Fig. 5 b.
Tiling comprises the X-ray detector 12 of independent detector element 12a, b, c, thus (22a, b, c) focus on towards x-ray source 2, x-ray source 2 carries out translation or Linear-moving simultaneously to make the surface normal vector of independent X-ray detector element 12a, b, c.Between the difference of the X-ray detector 12 needed for phase retrieval is irradiated, to move relative to focal spot 14, displacement and/or tilt detector, especially using focal spot 14 as rotating shaft or sloping shaft.By rotating accordingly or tilting, can be implemented in every bar geometry ray between whole Harvest time and only overlap once with the gap between sheet block.Therefore, can both phase retrieval be carried out for the whole detector region comprising detector 12a, b, c here, carry out phase retrieval in the image obtained like this after, just can't see with post gap.
Not shown grating G in Fig. 7 a-d
1, G
2and possible G
0, but as mentioned before, need them in independent image acquisition 7a, extra phase stepping between b, c, d.Rotary faulty photography synthesis movement according to Fig. 5 b is also feasible.
With reference now to Fig. 8, depict the one exemplary embodiment according to the method for gathering disparate images information of the present invention.
In fig. 8, depict a kind of method 30 for gathering disparate images information, comprise the steps: to gather 32 first contrast information under first phase step state, the displacement of 34X ray detector elements, inclination and/or rotation is made relative at least one in object and x-ray source, and make the displacement toward each other of beam splitter grating and analyser gratings, and under second phase step state, gather 36 second to match image information.Can for such as 9 acquisition step with different phase place step state separately altogether, step 34a, b and 36 are repeated x time, such as 8 times, to realize complete collection period, wherein between whole Harvest time, every bar geometry ray at most only overlaps once with the gap between sheet block.
In succession or simultaneously can carry out the displacement of displacement relative to the X-ray detector element of analyser gratings and beam splitter grating.
It should be pointed out that term " comprises " and do not get rid of other elements or step, indefinite article is not got rid of multiple.Also the element described in conjunction with different embodiment can be combined.
Should also be noted that the Reference numeral in claim should not be interpreted as limiting the scope of claim.
Claims (16)
1. the equipment for phase contrast imaging (1), comprising:
X-ray source (2);
There is the X-ray detector element (12) of detector size;
First optical grating element (8,10); And
Second optical grating element (8,10);
Wherein, object (6) can be arranged between described x-ray source (2) and described X-ray detector element (12);
Wherein, described first optical grating element (8,10) and described second optical grating element (8,10) can be arranged between described x-ray source (2) and described X-ray detector element (12);
Wherein, operatively be coupled described x-ray source (2), described first optical grating element (8,10), described second optical grating element (8, and described X-ray detector element (12), thus make it possible to the phase contrast image obtaining described object (6) 10);
Wherein, described equipment (1) is suitable for the disparate images that acquisition field of view is greater than described detector size;
Wherein, described X-ray detector element (12) can displacement; And
Wherein, by the displacement of described X-ray detector element (12), the disparate images of described visual field can be obtained,
Wherein, described X-ray detector element (12) is suitable for the subarea gathering described visual field; And
Wherein, when described X-ray detector element (12) is displaced to the second position in the second subarea for gathering described visual field from the primary importance in the first subarea for gathering described visual field, make described first optical grating element (8,10) and described second optical grating element (8,10) the Δ value that displacement is extra toward each other, to provide first phase step state in described first position and to provide second phase step state in described second position.
2. equipment according to claim 1,
Wherein, at least one comprising in the focal spot of described x-ray source (2) and described x-ray source (2) of the displacement of described X-ray detector element (12) rotates.
3. according to the equipment one of aforementioned claim Suo Shu,
Wherein, described first optical grating element and described second optical grating element are one of beam splitter grating (8) and analyser gratings (10);
Wherein, described first optical grating element (8,10) and described second optical grating element (8,10) can displacements toward each other, to provide phase place stepping; And/or
Wherein, described first optical grating element (8,10) and described second optical grating element (8,10) are arranged to parallel to each other and are parallel to described X-ray detector element (12).
4. equipment according to claim 1,
Wherein, described x-ray source (2) can relative to described first optical grating element (8,10), described second optical grating element (8,10) and/or described X-ray detector element (12) displacement.
5. equipment according to claim 1,
Wherein, described x-ray source (2), described first optical grating element (8,10), described second optical grating element (8,10) and described X-ray detector element (12) can rotate around described object (6).
6. according to the equipment one of claim 4 or 5 Suo Shu,
Wherein, at least one in described first optical grating element (8,10) and described second optical grating element (8,10) comprises groove structure;
Wherein, described groove structure comprises the first expansion being parallel to described groove structure and groove respectively; And
Wherein, the displacement of described x-ray source is parallel to described first expansion.
7. equipment according to claim 1, also comprises:
At least two X-ray detector elements (12a-e);
At least two the first optical grating elements (8,10); And
At least two the second optical grating elements (8,10);
Wherein, described at least two adjacent layouts of X-ray detector element (12a-e);
Wherein, described at least two X-ray detector elements (12a-e) separately spacing distance;
Wherein, the surface normal vector (22a-c) on each direction being included in described x-ray source (2) of described at least two X-ray detector elements (12a-e); And
Wherein, in described spacing distance, image information cannot be gathered.
8. equipment according to claim 7,
Wherein, described x-ray source (2) can around described object (6) displacement; And
Wherein, maintain during the displacement of described x-ray source (2) described in the orientation of described surface normal vector (22a-c) on the direction of described x-ray source (2) of at least two X-ray detector elements (12a-e).
9. according to the equipment one of claim 7 or 8 Suo Shu,
Wherein, described at least two X-ray detector elements (12a-e) can be displaced to the second position for gathering the second disparate images and/or orientation from the primary importance and/or orientation for gathering the first disparate images, and
Wherein, at least two the first optical grating elements (8 described in making, 10) each and described at least two the second optical grating elements (8,10) another each displacement toward each other corresponding, to provide first phase step state when gathering described first disparate images and to provide second phase step state when gathering described second disparate images.
10. the equipment according to claim 7 or 8,
Wherein, the displacement of at least two X-ray detector elements (12a-e), inclination and/or rotation described in the chien shih of collection two different disparate images, thus the image information that cannot gather in described spacing distance is minimized.
11. equipment according to claim 10,
Wherein, at least two X-ray detector elements (12a-e) displacement described in making during collection disparate images, inclination and/or rotation, thus every bar geometry ray is overlapped at most once with described spacing distance.
12. 1 kinds of x-ray systems, it comprises according to the equipment for phase contrast imaging (1) one of aforementioned claim Suo Shu.
13. 1 kinds for gathering the method (30) of disparate images information,
A; Under first phase step state, gather (32) first to match image information;
B; The displacement of X-ray detector element, inclination and/or rotation (34a) is made relative at least one in object and x-ray source, and make the first optical grating element (8,10) the Δ value that and the second optical grating element (8,10) displacement toward each other (34b) is extra; And
C; Under second phase step state, gather (36) second to match image information.
14. methods according to claim 13,
Wherein, by the number of times that step b and c re-defines, thus form collection period; And
Wherein, during described collection period, every bar geometry ray overlaps at most once with the gap between sheet block.
15. methods according to claim 14,
Wherein, step b and c is repeated 8 times, thus form collection period.
16. use according to the equipment for phase contrast imaging (1) one of claim 1 to 11 Suo Shu in x-ray system, one of CT system and tomography synthesis system.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| EP09178692 | 2009-12-10 | ||
| EP09178692.1 | 2009-12-10 | ||
| PCT/IB2010/055571 WO2011070493A1 (en) | 2009-12-10 | 2010-12-03 | Apparatus for phase-contrast imaging comprising a displaceable x-ray detector element and method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102655809A CN102655809A (en) | 2012-09-05 |
| CN102655809B true CN102655809B (en) | 2015-06-17 |
Family
ID=43667750
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201080055839.5A Expired - Fee Related CN102655809B (en) | 2009-12-10 | 2010-12-03 | Apparatus for phase-contrast imaging comprising a displaceable X-ray detector element and method |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US9066649B2 (en) |
| EP (1) | EP2509503B1 (en) |
| JP (1) | JP5759474B2 (en) |
| CN (1) | CN102655809B (en) |
| BR (1) | BR112012013696A8 (en) |
| RU (1) | RU2562879C2 (en) |
| WO (1) | WO2011070493A1 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107693039A (en) * | 2017-11-14 | 2018-02-16 | 广州华端科技有限公司 | X-ray detection device, cone-beam CT-systems and its imaging method |
Families Citing this family (29)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2008102685A1 (en) | 2007-02-21 | 2008-08-28 | Konica Minolta Medical & Graphic, Inc. | Radiological image picking-up device and radiological image picking-up system |
| CN103189739B (en) * | 2010-10-19 | 2015-12-02 | 皇家飞利浦电子股份有限公司 | Differential phase contrast's imaging |
| JP6060082B2 (en) * | 2010-10-19 | 2017-01-11 | コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． | Diffraction grating, system, apparatus, method, computer program and medium for differential phase contrast imaging |
| DE102011082878A1 (en) * | 2011-09-16 | 2013-03-21 | Siemens Aktiengesellschaft | X-ray detector of a grid-based phase-contrast X-ray device and method for operating a grid-based phase-contrast X-ray device |
| CN104066375B (en) * | 2012-01-24 | 2017-08-11 | 皇家飞利浦有限公司 | Multi-direction phase contrast x-ray imaging |
| WO2014137325A1 (en) * | 2012-03-05 | 2014-09-12 | University Of Rochester | Methods and apparatus for differential phase-contrast cone-beam ct and hybrid cone-beam ct |
| JP6149343B2 (en) * | 2012-03-26 | 2017-06-21 | コニカミノルタ株式会社 | Grating and grating unit and X-ray imaging apparatus |
| DE102012208305B4 (en) * | 2012-05-16 | 2022-10-20 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | X-ray detector and X-ray system |
| WO2014027289A1 (en) * | 2012-08-17 | 2014-02-20 | Koninklijke Philips N.V. | Handling misalignment in differential phase contrast imaging |
| JP6191136B2 (en) * | 2013-01-10 | 2017-09-06 | コニカミノルタ株式会社 | Image generation method |
| DE102013213244A1 (en) * | 2013-07-05 | 2015-01-08 | Siemens Aktiengesellschaft | X-ray system for the high-resolution differential phase-contrast imaging of an examination object |
| RU2663176C2 (en) * | 2013-09-30 | 2018-08-01 | Конинклейке Филипс Н.В. | Differential phase contrast imaging device with movable grating(s) |
| CN104622492A (en) * | 2013-11-11 | 2015-05-20 | 中国科学技术大学 | X-ray grating phase-contrast imaging device and method |
| DE102014221599A1 (en) | 2014-10-23 | 2016-04-28 | Siemens Aktiengesellschaft | Apparatus and method for X-ray phase-contrast imaging |
| EP3223707A1 (en) | 2014-11-24 | 2017-10-04 | Koninklijke Philips N.V. | Detector and imaging system for x-ray phase contrast tomo-synthesis imaging |
| CN104535595B (en) * | 2015-01-09 | 2017-05-31 | 中国科学技术大学 | A kind of background deduction method for X-ray grating phase contrast imaging |
| CN108271415B (en) | 2015-04-07 | 2019-03-05 | 深圳帧观德芯科技有限公司 | Semiconductor X-Ray detector |
| JP6415759B2 (en) * | 2015-06-15 | 2018-10-31 | コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． | Tile detector arrangement, apparatus, method, program element and storage medium for differential phase contrast CT |
| JP6626517B2 (en) * | 2015-06-26 | 2019-12-25 | コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． | Robust reconstruction for darkfield and phase contrast CT |
| WO2017015381A1 (en) * | 2015-07-20 | 2017-01-26 | Rensselaer Polytechnic Institute | X-ray phase-contrast and dark-field information extraction with electric fringe scanning and/or active pixel processing |
| EP3362819A4 (en) | 2015-10-14 | 2019-06-05 | Shenzhen Xpectvision Technology Co., Ltd. | X-ray detectors capable of limiting diffusion of charge carriers |
| US10973483B2 (en) | 2016-09-08 | 2021-04-13 | Koninklijke Philips N.V. | Phase-contrast and dark-field CT reconstruction algorithm |
| KR101873109B1 (en) | 2016-10-17 | 2018-06-29 | 경희대학교 산학협력단 | Two-dimensional x-ray detector, cone-beam ct apparatus and method using region-of-interest |
| CN107748341B (en) * | 2017-10-23 | 2024-08-13 | 中国科学院苏州生物医学工程技术研究所 | High-contrast low-dose phase contrast CT imaging device |
| EP3498170A1 (en) * | 2017-12-12 | 2019-06-19 | Koninklijke Philips N.V. | Device and method for aligning an x-ray grating to an x-ray radiation source, and x-ray image acquisition system |
| WO2019130848A1 (en) | 2017-12-26 | 2019-07-04 | 株式会社島津製作所 | X-ray imaging device |
| EP3654075A1 (en) | 2018-11-13 | 2020-05-20 | Koninklijke Philips N.V. | Structured grating component, imaging system and manufacturing method |
| EP3705044A1 (en) * | 2019-03-08 | 2020-09-09 | Koninklijke Philips N.V. | System for x-ray dark field; phase contrast and attenuation tomosynthesis image acquisition |
| CN111721786B (en) * | 2019-03-22 | 2023-05-26 | 中国科学院深圳先进技术研究院 | A kind of X-ray interferometer and imaging system |
Family Cites Families (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| RU2098797C1 (en) * | 1994-11-30 | 1997-12-10 | Алексей Владиславович Курбатов | Method for obtaining object projection by means of penetrating radiation and device for its realization |
| US5812629A (en) * | 1997-04-30 | 1998-09-22 | Clauser; John F. | Ultrahigh resolution interferometric x-ray imaging |
| RU2002116658A (en) * | 2002-06-24 | 2004-03-10 | Алексей Анатольевич Манушкин | Phase contrast radiography method and device for its implementation — small angle X-ray interferometer based on phase-modulating diffraction gratings |
| EP1623671A4 (en) * | 2002-12-26 | 2008-11-05 | Atsushi Momose | X-ray imaging system and imaging method |
| EP1447046A1 (en) * | 2003-02-14 | 2004-08-18 | Paul Scherrer Institut | Apparatus and method to obtain phase contrast x-ray images |
| EP1731099A1 (en) | 2005-06-06 | 2006-12-13 | Paul Scherrer Institut | Interferometer for quantitative phase contrast imaging and tomography with an incoherent polychromatic x-ray source |
| JP2006345290A (en) | 2005-06-09 | 2006-12-21 | Vanilla Studio:Kk | Method, system, and server device for document authentication |
| JP2006346290A (en) * | 2005-06-17 | 2006-12-28 | Konica Minolta Medical & Graphic Inc | Radiographic image photographing apparatus |
| DE102006015358B4 (en) | 2006-02-01 | 2019-08-22 | Paul Scherer Institut | Focus / detector system of an X-ray apparatus for producing phase-contrast images, associated X-ray system and storage medium and method for producing tomographic images |
| CN101576515B (en) * | 2007-11-23 | 2012-07-04 | 同方威视技术股份有限公司 | System and method for X-ray optical grating contrast imaging |
| US7693256B2 (en) | 2008-03-19 | 2010-04-06 | C-Rad Innovation Ab | Phase-contrast X-ray imaging |
-
2010
- 2010-12-03 CN CN201080055839.5A patent/CN102655809B/en not_active Expired - Fee Related
- 2010-12-03 JP JP2012542663A patent/JP5759474B2/en not_active Expired - Fee Related
- 2010-12-03 BR BR112012013696A patent/BR112012013696A8/en not_active Application Discontinuation
- 2010-12-03 EP EP10807374.3A patent/EP2509503B1/en not_active Not-in-force
- 2010-12-03 US US13/514,383 patent/US9066649B2/en not_active Expired - Fee Related
- 2010-12-03 WO PCT/IB2010/055571 patent/WO2011070493A1/en active Application Filing
- 2010-12-03 RU RU2012128794/14A patent/RU2562879C2/en not_active IP Right Cessation
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107693039A (en) * | 2017-11-14 | 2018-02-16 | 广州华端科技有限公司 | X-ray detection device, cone-beam CT-systems and its imaging method |
| CN107693039B (en) * | 2017-11-14 | 2019-03-08 | 广州华端科技有限公司 | X-ray detection device, cone-beam CT-systems and its imaging method |
Also Published As
| Publication number | Publication date |
|---|---|
| BR112012013696A2 (en) | 2018-05-08 |
| BR112012013696A8 (en) | 2018-05-29 |
| EP2509503A1 (en) | 2012-10-17 |
| US20120307966A1 (en) | 2012-12-06 |
| EP2509503B1 (en) | 2017-08-09 |
| US9066649B2 (en) | 2015-06-30 |
| WO2011070493A1 (en) | 2011-06-16 |
| JP2013513414A (en) | 2013-04-22 |
| CN102655809A (en) | 2012-09-05 |
| RU2012128794A (en) | 2014-01-20 |
| RU2562879C2 (en) | 2015-09-10 |
| JP5759474B2 (en) | 2015-08-05 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102655809B (en) | Apparatus for phase-contrast imaging comprising a displaceable X-ray detector element and method | |
| EP2611364B1 (en) | Differential phase-contrast imaging with improved sampling | |
| CN102656644B (en) | Non-parallel grating device with instant phase stepping, X-ray system and use | |
| US8831174B2 (en) | X-ray imaging method and X-ray imaging apparatus | |
| JP5702586B2 (en) | Radiography system | |
| US9084528B2 (en) | Phase contrast imaging | |
| EP2830505B1 (en) | Hybrid pci system for medical radiographic imaging | |
| EP3316782B1 (en) | Scanning x-ray apparatus with full-field detector | |
| WO2007125833A1 (en) | X-ray image picking-up device and x-ray image picking-up method | |
| JP2012090945A (en) | Radiation detection device, radiographic apparatus, and radiographic system | |
| CN107850680A (en) | For phase-contrast and/or the X-ray detector of dark-field imaging | |
| JP6148415B1 (en) | Computed tomography (CT) hybrid data collection | |
| JP2011206490A (en) | Radiographic system and radiographic method | |
| US20170303867A1 (en) | Detector and imaging system for x-ray phase contrast tomo-synthesis imaging | |
| JP2011206489A (en) | Radiographic system and radiographic method | |
| Sato et al. | Single-shot x-ray phase-contrast imaging using two-dimensional gratings |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20150617 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |